EP2415491A1 - Appareil de traitement sanguin extracorporel - Google Patents

Appareil de traitement sanguin extracorporel Download PDF

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Publication number
EP2415491A1
EP2415491A1 EP10008037A EP10008037A EP2415491A1 EP 2415491 A1 EP2415491 A1 EP 2415491A1 EP 10008037 A EP10008037 A EP 10008037A EP 10008037 A EP10008037 A EP 10008037A EP 2415491 A1 EP2415491 A1 EP 2415491A1
Authority
EP
European Patent Office
Prior art keywords
pump
line
chamber
blood
expansion chamber
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
EP10008037A
Other languages
German (de)
English (en)
Other versions
EP2415491B1 (fr
Inventor
Hiram Rada
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Gambro Lundia AB
Original Assignee
Gambro Lundia AB
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Gambro Lundia AB filed Critical Gambro Lundia AB
Priority to EP10008037.3A priority Critical patent/EP2415491B1/fr
Priority to ES10008037.3T priority patent/ES2496692T3/es
Priority to US13/196,009 priority patent/US8394047B2/en
Publication of EP2415491A1 publication Critical patent/EP2415491A1/fr
Priority to US13/780,308 priority patent/US8956317B2/en
Application granted granted Critical
Publication of EP2415491B1 publication Critical patent/EP2415491B1/fr
Not-in-force legal-status Critical Current
Anticipated expiration legal-status Critical

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/30—Single needle dialysis ; Reciprocating systems, alternately withdrawing blood from and returning it to the patient, e.g. single-lumen-needle dialysis or single needle systems for hemofiltration or pheresis
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
    • A61M1/1654—Dialysates therefor
    • A61M1/1656—Apparatus for preparing dialysates
    • A61M1/1666—Apparatus for preparing dialysates by dissolving solids
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/30—Single needle dialysis ; Reciprocating systems, alternately withdrawing blood from and returning it to the patient, e.g. single-lumen-needle dialysis or single needle systems for hemofiltration or pheresis
    • A61M1/301—Details
    • A61M1/302—Details having a reservoir for withdrawn untreated blood
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/30—Single needle dialysis ; Reciprocating systems, alternately withdrawing blood from and returning it to the patient, e.g. single-lumen-needle dialysis or single needle systems for hemofiltration or pheresis
    • A61M1/301—Details
    • A61M1/305—Control of inversion point between collection and re-infusion phase
    • A61M1/306—Pressure control, e.g. using substantially rigid closed or gas buffered or elastic reservoirs

Definitions

  • the invention relates to an extracorporeal blood treatment apparatus, which is advantageously usable in the treatment of CHF (Congestive Heart Failure).
  • CHF Consgestive Heart Failure
  • SCUF Small Continuous Ultra-Filtration
  • SCUF Slow Continuous Ultra-Filtration
  • a hemofilter an anticoagulation means (syringe pump)
  • a fluid removal device e.g. roller pump
  • safety devices air and blood leak detectors, pressure sensors, patient sensor
  • extracorporeal blood treatments such as hemodialysis, hemodiafiltration, hemoperfusion, etc.
  • blood circuits of the single needle type in which blood is withdrawn from, and returned to, the patient's circulatory system through a single needle with a Y-shaped junction.
  • blood may be alternately cycled from and to the patient's body by a single blood pump, or by arterial and venous blood pumps, respectively.
  • a first (withdrawal or arterial) phase of operation blood is drawn from the patient and pumped into the treatment device (exchanger of a semipermeable membrane type) by the arterial blood pump.
  • Blood is prevented from returning to the needle by the closure of a valve (clamp) located between the outlet of the arterial pump and the needle, or through a clamping action of the venous blood pump.
  • Blood pressure within the blood circuit builds until a time at which the arterial pump is turned off, the valve is opened, or the venous pump in a two-pump system is turned on to pump the blood out of the treatment device and back to the patient during a second (return or venous) phase of operation.
  • the venous phase is terminated and the cycle repeats.
  • the single needle system has the advantage of half the number of needle insertions, which may be psychologically attractive to the patient, as well as prolonging the life of the fistula into which the needle is normally inserted.
  • U.S. Patent No. US 4,231,366 discloses a single needle system used in connection with such treatments as blood dialysis, blood perfusion and blood diafiltration, in which an arterial blood pump operates during the blood withdrawal phase as well as during the blood return phase, whereas a venous blood pump only operates during the blood return phase with a pumping rate which is larger than the rate of the arterial pump.
  • the return blood flow pumped by the venous pump is divided in the junction member so that a proportion is returned to the patient through the needle and another proportion is pumped again by the arterial pump in accordance with the pumping rate of the arterial pump, whereby the blood is subjected repeatedly to a cleaning operation in the treatment device.
  • An aim of the present invention is to provide an apparatus which is able to perform a fluid removal therapy in a single needle mode.
  • a further aim of the invention is to make available a mode, particularly a single-needle mode, which is simpler than existing modes in order to perform a pure ultrafiltration blood treatment.
  • An advantage is achieving continuous blood circulation in the hemofilter (membrane device in which the pure ultrafiltration occurs) and avoiding excessive hemoconcentration therein.
  • Another advantage is reducing the noise during the treatment of pure ultrafiltration, particularly by avoiding the use of one or more clamps to block the blood flow in predefined portions of the extracorporeal blood circuit.
  • a further advantage is minimizing the extracorporeal blood volume of the blood circuit so as to perform a blood treatment (pure ultrafiltration) with a small extracorporeal blood volume.
  • a further advantage is to provide an extracorporeal blood treatment apparatus having an easy setup.
  • 1 denotes in its entirety an extracorporeal blood treatment apparatus configured to perform a fluid removal treatment (ultrafiltration-only treatment), in particular for the treatment of CHF (Congestive Heart Failure).
  • a fluid removal treatment ultrafiltration-only treatment
  • CHF Consgestive Heart Failure
  • the apparatus 1 comprises a single-needle extracorporeal blood circuit.
  • the blood circuit comprises a patient line 2 connected, in a known manner, to the single needle 3.
  • the patient line 2 has a three way junction, of known type (e.g. T-junction or Y-junction), for the connection to a first (arterial or withdrawal) line and a second (venous or return) line.
  • the patient line 2 and the first and second lines are configured to transport the blood.
  • the direction of the blood flow is indicated by an arrow.
  • the first line connects the patient line 2 to an inlet of a first chamber of a semipermeable membrane device 4 (e.g. hemofilter) in which the blood treatment (pure ultrafiltration) will occur.
  • the second line connects the patient line to an outlet of the first chamber of the membrane device 4.
  • the membrane device 4 has a semipermeable membrane which separates the first chamber from a second chamber.
  • the apparatus 1 comprises blood circulating means which comprises a first blood pump 5 arranged on the first line and a second blood pump 6 arranged on the second line.
  • the blood pumps 5 and 6 may be of the occlusive type (e.g. peristaltic pumps).
  • the apparatus 1 comprises an expansion chamber 7 arranged on the first line.
  • the expansion chamber 7 constitutes a compliance of the single-needle blood circuit.
  • the volume of the expansion chamber 7 should be significantly higher than the volume of the access line 2 between the junction and the needle 3.
  • the apparatus 1 comprises a first pressure measurement device 8 arranged to measure the pressure in a region of the blood circuit comprised between the needle 3 and the blood pumps 5 and 6.
  • the first pressure measurement device 8 may be connected to the patient line 2; alternatively the pressure sensor 8 may be connected either between the Y junction and blood pump 5 or between the Y junction and blood pump 6.
  • the apparatus 1 comprises a second pressure measurement device 9 arranged to measure the pressure in a further region of the blood circuit comprised between the blood pumps 5 and 6 and including the membrane device 4.
  • the second pressure measurement device 9 may be connected to the first line.
  • the second pressure measurement device 9 may be connected to the expansion chamber 7.
  • the pressure measurement devices 8 and 9 measure the pressure of the blood access proximal to the needle 3 and, respectively, the pressure inside the blood circuit proximal to the membrane device 4.
  • the apparatus 1 comprises an ultrafiltration circuit, of known type, which comprises an ultrafiltration line connected to an outlet of the second chamber of the membrane device 4.
  • the ultrafiltration circuit comprises an ultrafiltration pump 10 which provides the circulation of the fluid (ultrafiltrate) removed from the blood. The flow of the removed fluid goes from the outlet of the second chamber of the membrane device 4 to a drain 11.
  • the ultrafiltration circuit comprises an ultrafiltration pressure measurement device 12 arranged to measure the pressure in the ultrafiltration line between the membrane device 4 and the ultrafiltration pump 10.
  • the apparatus comprises a control unit which is connected to the actuators (pumps 5, 6, 10) and the sensors (pressure measurement devices 8, 9, 12) of the apparatus in order to control the operation thereof.
  • the control unit is configured to operate according to a predefined (software) program which comprises the instructions to perform the extracorporeal blood treatment method as below explained.
  • a single-needle extracorporeal blood circuit is achieved by alternatively switching from an arterial phase (during which the blood in withdrawn from the blood access) to a venous phase (during which the blood is returned to the patient).
  • Figure 2 illustrates the operation during the arterial phase.
  • the arterial phase is achieved by setting the flow rate of the first pump 5 higher than the flow rate of the second pump 6. The difference between the two flow rates results in a flow rate of blood coming from the patient.
  • the level of blood in the expansion chamber 7 increases and results in an increase of the pressure in the blood circuit as measured by the second pressure measurement device 9.
  • the switch to the venous phase is triggered when the pressure measured by the second pressure measurement device 9 reaches a pre-determined threshold value.
  • the blood flow in the membrane device 4 (from the inlet to the outlet of the first chamber of the membrane device 4) is substantially equal to the flow rate of the second pump 6 (neglecting the ultrafiltration flow rate actuated by the ultrafiltration pump 10 through the membrane of the membrane device 4).
  • Figure 3 illustrates the operation during the venous phase.
  • the flow rate of the first pump 5 is set lower than the flow rate of the second pump 6.
  • the blood level in the expansion chamber 7 decreases as well as the pressure in the blood circuit measured by the second pressure measurement device 9.
  • the venous phase ends when the pressure measured by the second pressure measurement device 9 decreases below a pre-determined threshold value.
  • the flow rate in the membrane device 4 (from the inlet to the outlet of the first chamber of the membrane device 4) is substantially equal to the flow rate of the pump 2 (neglecting the ultrafiltration flow rate).
  • Figure 4 gives a representation of the alternation of the two pump flow rates between the arterial phase and the venous phase and the corresponding variations in the blood circuit pressure (the pressure measured by the second pressure measurement device 9).
  • the switch between the arterial phase and the venous phase may be triggered by using pressure signals, in particular when the maximum and minimum threshold pressures are reached.
  • a level detector operatively connected to the expansion chamber 7 may be used to trigger the switching from one phase to another phase.
  • the control unit may be programmed to switch between the two phases when maximum and minimum threshold blood levels in the expansion chamber 7 are reached.
  • FIG. 5 shows an alternative single needle blood treatment apparatus which achieves the single-needle functionality in a different manner.
  • the ultrafiltration circuit may be the same as in the apparatus of Figure 1 .
  • the same elements of the apparatus of Figure 1 have been indicated with the same numeral reference.
  • the apparatus of Figure 5 will be provided with a control unit as for the apparatus of Figure 1 .
  • the apparatus of Figure 5 comprises an air pump 13 connected to the expansion chamber 7.
  • the air pump 13 may replace one of two pumps 5 or 6 of the apparatus of Figure 1 .
  • the first pump 5 upstream the membrane device 4
  • the second pump 6 downstream the membrane device 4
  • the second pump 6 has been functionally replaced by the air pump 13 operating on the expansion chamber 7.
  • the first pump 5 upstream the membrane device 4)
  • the second pump 6 may be present.
  • the blood pump that is present (the first pump 5 in Figure 5 ) will operate to ensure the continuous circulation of the blood in the blood circuit.
  • the air pump 13 may alternately operate in both directions so as to alternately empty and fill the expansion chamber 7.
  • the air pump 13 will operate to control the blood level in the expansion chamber 7.
  • the air pump 13 allows to alternate the arterial phase and the venous phase by alternatively emptying and filling the expansion chamber 7.
  • the control of the air pump 13, as well as of the first pump 5) may be based on information on the situation in the expansion chamber 7.
  • the air pump 13 may be controlled on the basis of pressure signals received from the second pressure measurement device 9, or on the basis of blood level signals received from a blood level sensor associated to the expansion chamber 7.
  • the first pump 5 may be controlled so as to pump an arterial flow rate during the arterial phase and a venous flow rate during the venous phase, in which the arterial flow rate is higher than the venous flow rate.
  • the first pump 5 and the air pump 13 maybe controlled so as to maintain substantially the same flow rate in the first chamber of the membrane device 4 both in the arterial and in the venous phase.
  • the (arterial) expansion chamber 7 of Figures 1 and 5 may be arranged in the second (venous) line.
  • the (venous) expansion chamber will be arranged upstream the second pump 6 (between the device 4 and the pump 6), and in a second case, analogous to the case of Figure 5 , the (venous) expansion chamber will be operatively associated to an air pump as the pump 13 and, optionally, to a pressure measurement device as the device 9.
  • the first pump 5 may operate at a constant rate while the second pump 6 may alternate a withdrawal phase at a less rate than the first pump 5 and a return phase at a greater rate than the first pump 5.
  • the first pump 5 may operate at a constant rate while the reversal air pump may alternate a withdrawal phase at a predefined rate in a suction (air emptying) mode and a return phase at a predefined rate in a pumping (air filling) mode.
  • the first line and the second line are configured so that during the withdrawal phase and during the return phase the blood flow in the second line can freely and partially recirculate into the first line through the three-way junction.
  • no clamps or other clamp means is provided in the first line between the first pump 5 and the three way junction and/or in the second line between the second pump 6 or 13 and the three way junction.
  • the extracorporeal blood treatment apparatus may be provided with means, of known type, for anticoagulation of the blood.
  • An air bubble detector is usually placed downstream the membrane device 4 to detect the dangerous presence of air bubbles in the blood and allowing in such a case putting the apparatus in safe condition for the patient.
  • a blood leak detector might be associated to the ultrafiltration circuit, for example before or after the pressure device 12.
  • the method may further comprise one or more of the following steps, in any combination thereof: no clamp means is operated to clamp said first line between said first pump 5 and said three way junction and/or said second line between said second pump 6; 13 and said three way junction; connecting said first pump 5 to said first line and said second pump 6 to said second line, arranging said expansion chamber 7 downstream said first pump 5 and upstream said second pump 6, and controlling said first pump at a flow rate higher than a flow rate of said second pump during said withdrawal phase and less than a flow rate of said second pump during said return phase; controlling said second pump 6 at a same constant flow rate during said withdrawal and return phases; connecting said second pump, which comprises an air pump 13, to said expansion chamber 7, controlling said air pump so as to suck air from said expansion chamber 7 during said withdrawal phase and to pump air into said expansion chamber 7 during said return phase; connecting said first pump 5 to said first line, connecting said expansion chamber 7 to said first line downstream said first pump 5, controlling said first pump 5 at a flow rate during said withdrawal phase that is higher than a flow rate during said return phase;
  • the membrane device, the extracorporeal blood circuit and the ultrafiltration line may be configured to form a single disposable unit.

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  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Urology & Nephrology (AREA)
  • Anesthesiology (AREA)
  • Vascular Medicine (AREA)
  • Engineering & Computer Science (AREA)
  • Emergency Medicine (AREA)
  • Biomedical Technology (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • External Artificial Organs (AREA)
EP10008037.3A 2010-08-02 2010-08-02 Appareil de traitement sanguin extracorporel Not-in-force EP2415491B1 (fr)

Priority Applications (4)

Application Number Priority Date Filing Date Title
EP10008037.3A EP2415491B1 (fr) 2010-08-02 2010-08-02 Appareil de traitement sanguin extracorporel
ES10008037.3T ES2496692T3 (es) 2010-08-02 2010-08-02 Aparato de tratamiento sanguíneo extracorpóreo
US13/196,009 US8394047B2 (en) 2010-08-02 2011-08-02 Extracorporeal blood treatment apparatus
US13/780,308 US8956317B2 (en) 2010-08-02 2013-02-28 Extracorporeal blood treatment apparatus

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
EP10008037.3A EP2415491B1 (fr) 2010-08-02 2010-08-02 Appareil de traitement sanguin extracorporel

Publications (2)

Publication Number Publication Date
EP2415491A1 true EP2415491A1 (fr) 2012-02-08
EP2415491B1 EP2415491B1 (fr) 2014-06-04

Family

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Family Applications (1)

Application Number Title Priority Date Filing Date
EP10008037.3A Not-in-force EP2415491B1 (fr) 2010-08-02 2010-08-02 Appareil de traitement sanguin extracorporel

Country Status (3)

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US (2) US8394047B2 (fr)
EP (1) EP2415491B1 (fr)
ES (1) ES2496692T3 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2014118021A1 (fr) * 2013-01-29 2014-08-07 Fresenius Medical Care Deutschland Gmbh Dispositif extracorporel de traitement du sang fonctionnant avec un seul raccordement au patient, et procédé permettant de faire fonctionner un dispositif extracorporel de traitement du sang fonctionnant avec un seul raccordement au patient

Families Citing this family (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3142723B1 (fr) * 2014-05-13 2018-07-04 Monica Zanotti Appareil d'hémo(dia)filtration à aiguille unique
EP2965770A1 (fr) * 2014-07-09 2016-01-13 Universitätsklinikum Regensburg Dispositif d'oxygénation du sang
US9486590B2 (en) 2014-09-29 2016-11-08 Fenwal, Inc. Automatic purging of air from a fluid processing system
US9498567B2 (en) 2014-09-29 2016-11-22 Fenwal, Inc. Systems and methods for controlling the return phase of a blood separation procedure
JP5986258B1 (ja) * 2015-04-20 2016-09-06 日機装株式会社 血液浄化装置
WO2017001358A1 (fr) 2015-06-29 2017-01-05 Gambro Lundia Ab Circuit sanguin extracorporel pour traitements en aiguille unique

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4231366A (en) 1976-08-12 1980-11-04 Dr. Eduard Fresenius Chemisch-Pharmazeutische Industrie Kg Apparatebau Kg Blood flow monitoring and control apparatus
EP0229271A2 (fr) * 1986-01-14 1987-07-22 B. Braun-SSC AG Dispositif de dialyse
EP0472480A1 (fr) * 1990-08-20 1992-02-26 Hospal Industrie Circuit à aiguille unique pour faire circuler le sang en dehors du corps vers un appareil de traitement du sang
US5098373A (en) * 1989-07-19 1992-03-24 Fresenius Ag Process for controlling blood pumps in the extra-corporeal circuit of a single needle arrangement and apparatus thereof
WO2008148505A2 (fr) * 2007-06-04 2008-12-11 Fresenius Medical Care Deutschland Gmbh Dispositif et procédé de traitement du sang en mode une aiguille
WO2010037520A1 (fr) * 2008-10-02 2010-04-08 Fresenius Medical Care Deutschland Gmbh Dispositif pour le traitement extracorporel du sang, en fonctionnement à une seule aiguille

Family Cites Families (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4464164A (en) 1982-09-24 1984-08-07 Extracorporeal Medical Specialties, Inc. Flowrate control for a blood flow system
US4490135A (en) * 1982-09-24 1984-12-25 Extracorporeal Medical Specialties, Inc. Single needle alternating blood flow system
US4498983A (en) 1983-05-26 1985-02-12 Baxter Travenol Laboratories, Inc. Pressure cuff draw mode enhancement system and method for a single needle blood fractionation system
US7540958B2 (en) * 2004-03-08 2009-06-02 Gambro Lundia Ab Device for controlling blood circulation for a single needle circuit

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4231366A (en) 1976-08-12 1980-11-04 Dr. Eduard Fresenius Chemisch-Pharmazeutische Industrie Kg Apparatebau Kg Blood flow monitoring and control apparatus
EP0229271A2 (fr) * 1986-01-14 1987-07-22 B. Braun-SSC AG Dispositif de dialyse
US5098373A (en) * 1989-07-19 1992-03-24 Fresenius Ag Process for controlling blood pumps in the extra-corporeal circuit of a single needle arrangement and apparatus thereof
EP0472480A1 (fr) * 1990-08-20 1992-02-26 Hospal Industrie Circuit à aiguille unique pour faire circuler le sang en dehors du corps vers un appareil de traitement du sang
WO2008148505A2 (fr) * 2007-06-04 2008-12-11 Fresenius Medical Care Deutschland Gmbh Dispositif et procédé de traitement du sang en mode une aiguille
WO2010037520A1 (fr) * 2008-10-02 2010-04-08 Fresenius Medical Care Deutschland Gmbh Dispositif pour le traitement extracorporel du sang, en fonctionnement à une seule aiguille

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2014118021A1 (fr) * 2013-01-29 2014-08-07 Fresenius Medical Care Deutschland Gmbh Dispositif extracorporel de traitement du sang fonctionnant avec un seul raccordement au patient, et procédé permettant de faire fonctionner un dispositif extracorporel de traitement du sang fonctionnant avec un seul raccordement au patient
US9821104B2 (en) 2013-01-29 2017-11-21 Fresenius Medical Care Deutschland Gmbh Extracorporeal blood treatment device for operation with a single patient connection and method for operation of an extracorporeal blood treatment device with a single patient connection

Also Published As

Publication number Publication date
US20130178781A1 (en) 2013-07-11
ES2496692T3 (es) 2014-09-19
US8956317B2 (en) 2015-02-17
US20120029409A1 (en) 2012-02-02
US8394047B2 (en) 2013-03-12
EP2415491B1 (fr) 2014-06-04

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